System and method for remotely monitoring at least one physiological characteristic of a child

ABSTRACT

There is disclosed a system and method for remotely monitoring at least one physiological condition of a child by detecting very low frequency acoustic signals. The apparatus comprises a sensor that is capable of detecting low frequency acoustic signals in the frequency range of one tenth Hertz to thirty Hertz. The sensor comprises a chamber having portions that form a cavity and a low frequency microphone placed within the cavity. An alternate embodiment of the invention comprises a chamber having portions that form a resonant cavity, a microphone mounted in the resonant cavity, and a membrane that covers the resonant cavity. Low frequency acoustic signals that are incident on the membrane cause the membrane to move and amplify the acoustic signals within the resonant cavity. The sensor provides information concerning physiological conditions of the child, such as respiration and cardiac activity. The sensor in a physiological condition monitor does not need to be directly coupled to the skin of the child being monitored.

RELATED APPLICATIONS

A related patent application by M. E. Halleck and M. D. Halleck has beenfiled concurrently with this patent application Ser. No. 09/534,813entitled “Apparatus and Method for Detecting Very Low Frequency AcousticSignals”. Another related patent application by M. E. Halleck and M. D.Halleck has been filed concurrently with this patent application Ser.No. 09/536,104 entitled “Sensor and Method for Detecting Very LowFrequency Acoustic Signals”. Another related patent application by M. E.Halleck, M. D. Halleck, M. L. Lehrman and A. R. Owens has been filedconcurrently with this patent application Ser. No. 09/536,093 entitled“Physiological Condition Monitors Utilizing Very Low Frequency AcousticSignals”. Another related patent application by M. E. Halleck, M. D.Halleck and G. V. Halleck has been filed concurrently with this patentapplication Ser. No. 09/535,293 entitled “System and Method for SeizingA Communication Channel in A Commercially Available Child Monitor”.

TECHNICAL FIELD OF THE INVENTION

The present invention is directed to physiological condition monitorsthat utilize very low frequency acoustic signals to detect cardiacactivity and respiration activity in children. The immediate detectionof a child's irregular heartbeat or the cessation of the child'srespiration can be used to prevent the death of the child. The presentinvention is directed to an apparatus and method for detecting very lowfrequency acoustic signals that represent physiological activity. Thepresent invention comprises a sensor and a method for detecting very lowfrequency acoustic signals in the frequency range of one tenth Hertz(0.1 Hz) to thirty Hertz (30.0 Hz). The sensor of the present inventionis capable of obtaining physiological condition signals from a childwithout being directly coupled to the skin of the child.

BACKGROUND OF THE INVENTION

In the United States an estimated two thousand to three thousand infantsa year suddenly die from unexplained causes. Apparently healthy childrencan suddenly die without any obvious cause of death. This phenomenon isknown as Sudden Infant Death Syndrome. In the United States SuddenInfant Death Syndrome is the leading cause of death of children betweenthe age of one month and one year. It is second only to congenitalabnormalities as the leading overall cause of death for all childrenless than one year of age.

If a child begins to experience difficulty in breathing or begins toexperience irregular heartbeat, whoever is caring for the child (usuallyone of the child's parents) may have only a few seconds to respond tothe child's distress. Therefore, it is very desirable to be able toprovide a child's care giver with immediate notification that the childis experiencing cardiac or respiratory difficulty. This may be achievedby using a physiological condition monitor that is capable ofcontinuously monitoring the physiological conditions of the child.

Microphones in physiological condition monitors are used to detectsounds that are indicative of physiological processes. Physiologicalcondition monitors are capable of obtaining and recording signalsindicative of a child's physiological processes. The most commonlymonitored physiological processes are respiration and cardiac activity.Physiological condition monitors that monitor respiration and cardiacactivity usually comprise one or more sensors coupled to the body of thechild whose physiological conditions are to be measured. The sensors arecapable of sensing changes in physical parameters that are caused by thechild's respiration and cardiac activity. Physiological conditionmonitors measure and record waveform signals received from the sensors.Electrocardiogram (ECG) waveform signals may be used to measure achild's cardiac activity. Respiration waveform signals may beelectronically derived using techniques such as impedance pneumongraphyor inductive plethysmography. Respiration waveform signals are used tomeasure a child's breathing rate and other types of informationconcerning respiration.

The present invention comprises a chamber and a microphone that iscapable of detecting very low frequency acoustic signals. The presentinvention is capable of monitoring physiological conditions in childrenutilizing very low frequency acoustic signals. For purposes ofillustration, the present invention will be described with reference tophysiological condition monitors that are capable of monitoringrespiration and cardiac activity. It is understood, however, that thepresent invention is not limited to use in respiration monitors, and isnot limited to use in cardiac activity monitors, and is not limited touse in physiological condition monitors in general. The presentinvention may be used to detect, measure and record any type of very lowfrequency acoustic signal.

Low heart rate is referred to as bradycardia. High heart rate isreferred to as tachycardia. Cessation of respiration is referred to asapnea. When a child exhibits apnea, bradycardia or tachycardia, a lifethreatening condition very likely exists. Physiological conditionmonitors that are capable of continuously monitoring a child'srespiration and cardiac activity are extremely useful for quicklydetecting apnea, bradycardia or tachycardia. Such physiologicalcondition monitors are also useful for quickly detecting other abnormalconditions such as a very slow breathing rate or a very high breathingrate.

Children who are susceptible to Sudden Infant Death Syndrome are knownto exhibit apnea and bradycardia. Physiological condition monitors thatare capable of continually monitoring respiration and cardiac activityare particularly useful in the early detection of apnea or bradycardiain children. Most physiological condition monitors are equipped with analarm system to sound an alert when such conditions are detected.

A physiological condition monitor may be coupled directly to a childwhile the child is sleeping in a bed. In such an arrangement thewaveform signals from the sensors coupled to the child's body may besent through wires directly to a detector circuit (and other circuitry)located in a console by the child's bed. The wires attached to the childrestrict the child's movements and frequently become tangled as thechild moves. The tangling of the wires can also result in the sensorsbecoming detached from the child. The loss of sensor contact can set offan alarm signal.

In other cases it is more practical to provide one or more sensorslocated in a belt, harness or item of clothing that is to be worn by thechild. In this type of physiological condition monitor the waveformsignal information from the sensors is transmitted via a radio frequencytransmitter to a radio frequency receiver in a base station unit that islocated away from the site of the physiological condition sensors. Thebase station unit contains circuitry for analyzing and recording thewaveform signal information. The base station unit contains circuitryfor detecting abnormal conditions in the child's breathing (such asapnea) or abnormal conditions in the child's cardiac activity (such asbradycardia or tachycardia). Because of the freedom of movement thatthis type of monitor provides, it is the preferred type of monitor formonitoring the physiological conditions of children.

If the data that is acquired by the physiological condition monitor isnot transmitted to the base station unit and recorded there, then thedata may be recorded in a memory data storage device located within thephysiological condition monitor. To preserve the freedom of movementthat is provided by a monitor that is worn on a belt, harness or item ofclothing, the memory data storage device within the physiologicalcondition monitor must be battery powered.

Electrocardiogram (ECG) waveform signals may be used to obtaininformation concerning a child's cardiac activity. To obtain ECGwaveforms an ECG sensor unit is coupled to the child. The ECG sensorunit is coupled to the child via electrodes capable of receiving cardiacactivity signals directly from the child's body.

In such an arrangement the electrodes must be attached directly to thechild's skin in order to receive the signals. The ECG sensor unitreceives the ECG electrical signals from the electrodes. The ECG signalsreceived by the ECG sensor unit are then either recorded within thephysiological condition monitor or transmitted to a base station unit.

It is possible to obtain information about cardiac activity fromacoustic signals. For example, U.S. Pat. No. 4,306,567 to Krasnerdiscloses a sensor apparatus coupled directly to the skin of a person.The Krasner sensor apparatus is capable of detecting acoustic signalsfrom cardiac contractions within a frequency bandwidth between aboutthirty Hertz (30.0 Hz) and ninety

Hertz (90.0 Hz). The acoustical energy associated with the cardiaccontractions detected by the Krasner sensor apparatus exhibits a maximumsignal-to-noise ratio at about forty five Hertz (45.0 Hz)

The Krasner sensor apparatus is also capable of detecting acousticsignals from breathing activity within a frequency bandwidth betweenabout three hundred Hertz (300.0 Hz) and six hundred Hertz (600.0 Hz).The acoustical energy associated with the breathing activity detected bythe Krasner sensor exhibits a maximum signal-to-noise ratio at aboutfour hundred Hertz (400.0 Hz). The Krasner sensor simultaneously detectsboth the cardiac activity signals at about forty five Hertz (45.0 Hz)and the breathing activity signals at about four hundred Hertz (400.0Hz) with a single sensor unit coupled directly to the skin.

Acoustic signals normally contain noise artifacts. We have determinedthat most of the noise artifacts present in acoustic signals due torespiration and cardiac activity may be eliminated by considering onlythe very low frequency components of acoustic signals. In particular,almost all noise artifacts that are present in acoustic signals that aredue to respiration and cardiac activity may be totally eliminated byfiltering out all components of the signal that are outside thefrequency range of one tenth Hertz (0.1 Hz) to thirty Hertz (30.0 Hz).This is due to the fact that most noise artifacts occur at frequenciesthat are higher than these frequencies.

We have also determined that sensor devices capable of detecting signalsin the very low acoustic frequency range of one tenth Hertz (0.1 Hz) tothirty Hertz (30.0 Hz) do not need to be coupled directly to the skin ofthe child whose physiological conditions are being monitored. A sensordevice that detects acoustic signals in the very low acoustic frequencyrange of one tenth Hertz (0.1 Hz) to thirty Hertz (30.0 Hz) inaccordance with the principles of the present invention is capable ofdetecting the acoustic signals from the child's body through the child'sclothes.

For these reasons it is advantageous to be able to detect very lowfrequency acoustic signals in the range of one tenth Hertz (0.1 Hz) tothirty Hertz (30.0 Hz). It is also advantageous to have an apparatus formonitoring physiological conditions in which it is not necessary tocouple a sensor unit directly to the skin of the child being monitored.It is also advantageous to have an apparatus for monitoringphysiological conditions which is capable of detecting acoustic signalsthrough the child's clothes.

SUMMARY OF THE INVENTION

The present invention comprises an improved physiological conditionmonitor that is capable of detecting very low frequency acoustic signalsin the range of one tenth Hertz (0.1 Hz) to thirty Hertz (30.0 Hz). Thevery low frequency acoustic signals are useful in monitoringphysiological conditions in children such as respiration and cardiacactivity. The present invention is capable of detecting signals in afrequency range that is lower than the range of frequencies previouslyused to detect acoustic signals for monitoring physiological conditions.

An advantageous embodiment of the present invention comprises a chamberand a microphone that is capable of detecting very low frequencyacoustic signals in the range of one tenth Hertz (0.1 Hz) to thirtyHertz (30.0 Hz). An advantageous embodiment of the chamber of thepresent invention comprises a closed chamber containing a fluid. Thefluid may be either a liquid or a gas. In most instances the fluid thatis used is air. The walls of the chamber are not completely rigid. Thewalls of the chamber are capable of expanding and contracting (i.e.,moving inwardly and outwardly with respect to the interior cavity of thechamber) in response to external inputs of mechanical energy that formwaves of very low frequency acoustical energy within the chamber.

The mechanical energy from outside the chamber forms waves of very lowfrequency acoustical energy within the chamber and causes the walls ofthe chamber to expand and contract by extremely small amounts. Theextremely small expansions and contractions of the walls of the chambercause the molecules of fluid in the chamber (usually molecules of air)to move in low frequency acoustic waves throughout the cavity of thechamber.

The present invention further comprises a microphone within the chamber.The microphone is capable of detecting the low frequency acoustic wavesof the molecules of fluid in the chamber that are caused by themechanical energy that causes the walls of the chamber to expand andcontract.

Prior art acoustic sensors directly detect higher frequency sounds thatare made by the lungs during respiration or by the heart during cardiacactivity. The sensor of the present invention, however, obtainsinformation by detecting very low frequency signals caused by the motionof the chest during respiration and by detecting very low frequencysignals associated with cardiac activity. Almost all of the noisecomponents in an acoustic signal have frequencies that are above thevery low frequency range. By using the method of the present inventionto exclude the higher frequencies of sound (and noise), the sensor ofthe present invention eliminates almost all the noise artifacts from-theacoustic signal.

The present invention is capable of detecting acoustic signals fromcardiac activity within a frequency bandwidth between about ten Hertz(10.0 Hz) and thirty Hertz (30.0 Hz). The acoustical energy associatedwith the cardiac activity detected by the present invention exhibits amaximum signal-to-noise ratio at about sixteen Hertz (16.0 Hz).

The present invention is capable of detecting acoustic signals fromrespiration within a frequency bandwidth between about one tenth Hertz(0.1 Hz) and two Hertz (2.0 Hz). The acoustical energy associated withthe respiration detected by the present invention exhibits a maximumsignal-to-noise ratio at about one and one half Hertz (1.5 Hz).

It is a primary object of the present invention to provide an improvedapparatus and method for detecting very low frequency acoustic signalsin the frequency range of one tenth Hertz (0.1 Hz) to thirty Hertz (30.0Hz).

It is also an object of the present invention to provide an improvedphysiological condition monitor that is capable of detecting very lowfrequency acoustic signals in the frequency range of one tenth Hertz(0.1 Hz) to thirty Hertz (30.0 Hz) indicative of physiologicalconditions.

It is also an object of the present invention to provide an improvedphysiological condition monitor with a sensor unit capable of detectingvery low frequency acoustic signals indicative of physiologicalconditions in a child where the sensor unit is not coupled directly tothe skin of the child being monitored.

It is also an object of the present invention to provide an improvedphysiological condition monitor with a sensor unit capable of detectingvery low frequency acoustic signals indicative of physiologicalconditions in a child where the sensor unit is capable of detecting suchsignals through the clothes of the child being monitored.

It is also an object of the present invention to provide an improvedphysiological condition monitor capable of detecting acoustic signalsfrom cardiac activity of a child within a frequency bandwidth betweenabout ten Hertz (10.0 Hz) and thirty Hertz (30.0 Hz).

It is a further object of the present invention to provide an improvedphysiological condition monitor capable of detecting acoustic signalsfrom respiration of a child within a frequency bandwidth between aboutone tenth Hertz (0.1 Hz) and two Hertz (2.0 Hz).

The foregoing has outlined rather broadly the features and technicaladvantages of the present invention so that those skilled in the art maybetter understand the detailed description of the invention thatfollows. Additional features and advantages of the invention will bedescribed hereinafter that form the subject of the claims of theinvent-ion. Those skilled in the art should appreciate that they mayreadily use the conception and the specific embodiment disclosed as abasis for modifying or designing other structures for carrying out thesame purposes of the present invention. Those skilled in the art shouldalso realize that such equivalent constructions do not depart from thespirit and scope of the invention in its broadest form.

Before undertaking the Detailed Description, it may be advantageous toset forth definitions of certain words and phrases used throughout thispatent document: the terms “include” and “comprise” and derivativesthereof mean inclusion without limitation; the term “or,” is inclusive,meaning and/or; the phrases “associated with” and “associatedtherewith,” as well as derivatives thereof, may mean to include, beincluded within, interconnect with, contain, be contained within,connect to or with, couple to or with, be communicable with, cooperatewith, interleave, juxtapose, be proximate to, be bound to or with, have,have a property of, or the like; and the term “controller” means anydevice, system or part thereof that controls at least one operation,such a device may be implemented in hardware, firmware, or software, orsome combination of at least two of the same. It should be noted thatthe functionality associated with any particular controller may becentralized or distributed, whether locally or remotely. Definitions forcertain words and phrases are provided throughout this patent document.Those of ordinary skill in the art should understand that in many, ifnot most, instances, such definitions apply to prior, as well as futureuses of such defined words and phrases.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, and theadvantages thereof, reference is now made to the following descriptionstaken in conjunction with the accompanying drawings, wherein likenumbers designate like objects, and in which:

FIG. 1 is a partially cutaway view showing one embodiment of the sensorof the present invention and showing the sensor chamber as a tube andshowing the placement of the microphone of the present invention in oneof the side walls of the sensor chamber; and

FIG. 2 is a partially cutaway view showing another embodiment of thesensor of the present invention and showing the sensor chamber as a tubeand showing the placement of the microphone of the present invention inone of the end walls of the sensor chamber; and

FIG. 3 is a partially cutaway view showing another embodiment ofthe-sensor of the present invention and showing the sensor chamber as atube with one open end and showing the placement of the microphone ofthe present invention in the closed end of the sensor chamber; and

FIG. 4 is an exploded view showing another embodiment of the sensor ofthe present invention and showing the sensor chamber as a rectangularbox and showing the placement of the microphone of the present inventionwithin the rectangular box; and

FIG. 5 is a cross sectional view of the embodiment of the sensor of thepresent invention shown in FIG. 4 taken along line 5—5 of FIG. 4; and

FIGS. 6A, 6B and 6C are circuit diagrams of an advantageous embodimentof circuitry for processing electrical signals from the microphone ofthe present invention; and

FIG. 7 is a block diagram of an advantageous embodiment of aphysiological condition monitor of the present invention; and

FIG. 8 is a perspective top view of an advantageous embodiment of themonitor housing of the physiological condition monitor of the presentinvention; and

FIG. 9 is a perspective bottom view of the advantageous embodiment ofthe monitor housing of the physiological condition monitor of thepresent invention shown in FIG. 8; and

FIG. 10 is an exploded perspective top view of the monitor housing ofthe physiological condition monitor showing the interconnection of thecomponents of the monitor housing; and

FIG. 11 is a plan view of the top housing of the monitor housing; and

FIG. 12 is a plan view of the bottom of the assembled physiologicalcondition monitor; and

FIG. 13 is a cross sectional view of the top housing of the monitorhousing taken along line 13—13 of FIG. 11; and

FIG. 14 is a cross sectional view of the top housing of the monitorhousing taken along line 14—14 of FIG. 11; and

FIG. 15 is a plan view of the bottom housing of the monitor housing; and

FIG. 16 is a side elevation view of the bottom housing of the monitorhousing taken along line 16—16 of FIG. 15; and

FIG. 17 is an end elevation view of the bottom housing of the monitorhousing taken along line 17—17 of FIG. 15; and

FIG. 18 is a plan view of the battery door of the monitor housing; and

FIG. 19 is a side elevation view of the battery door of the monitorhousing taken along line 19—19 of FIG. 18; and

FIG. 20 is an end elevation view of the battery door of the monitorhousing taken along line 20—20 of FIG. 18; and

FIG. 21 is a perspective bottom view of the monitor housing showing thebattery door in an open position and showing the placement of a batteryin the monitor housing.

DETAILED DESCRIPTION

FIGS. 1 through 21, discussed below, and the various embodiments used todescribe the principles of the present invention in this patent documentare by way of illustration only and should not be construed in any wayto limit the scope of the invention. Those skilled in the art willunderstand that the principles of the present invention may beimplemented in a suitably modified sensor or in a suitably modifiedphysiological condition monitor.

FIG. 1 is a partially cutaway view showing an advantageous embodiment ofsensor 100 of the present invention. Sensor 100 comprises a chamber 120and a microphone 110. In this embodiment chamber 120 comprises a hollowtube having side walls 130 and end walls 140 that form cavity 150 withinchamber 120. Cavity 150 of chamber 120 is filled with a fluid (notshown). The connections between side walls 130 and end walls 140 aresealed to prevent the escape of the fluid from cavity 150. The fluid maybe either a liquid or a gas. In most instances the fluid that is used isair.

When the fluid that is used is air, the connections between side walls130 and end walls 140 are not hermetically sealed. A small amount of airmay pass through the connections between side walls 130 and end walls140 to adjust for variations in ambient air pressure in the atmosphere.

Microphone 110 is mounted within chamber 120 so that the face 160 ofmicrophone 110 is within the fluid in cavity 150 of chamber 120.Microphone 110 may be mounted at any position within chamber 120. In oneadvantageous embodiment of the present invention shown in FIG. 1microphone 110 is mounted within one of the side walls 130 of chamber120. In an alternate advantageous embodiment of the present inventionshown in FIG. 2 microphone 110 is mounted within one of the end walls140 of chamber 120. Microphone 110 also has microphone output cables,170 and 180, for coupling microphone 110 to other electronic equipment(not shown in FIG. 1 or FIG. 2).

The side walls 130 (and end walls 140) of chamber 120 are constructed ofmaterial that is not completely rigid. The material used to constructthe walls, 130 and 140, may be thin metal or plastic. Because the walls,130 and 140, are not completely rigid, they are capable of expanding andcontracting (i.e., moving inwardly and outwardly) with respect to theinterior of cavity 150 of chamber 120. The ability of the walls, 130 and140, of sensor 100 to expand and contract in response to the presence ofwaves of low frequency acoustical energy in chamber 120 is a key featureof the present invention.

When acoustical energy from a source (not shown) reaches chamber 120 ofsensor 100 the acoustical energy contains both high frequency acousticsignal components and low frequency acoustic signal components. Thewalls 130 and the end walls 140 of chamber 120 of sensor 100 expand andcontract in response to the presence of the very low frequency acousticsignal components. The presence of waves of very low frequency acousticenergy in chamber 120 of sensor 100 cause the walls, 130 and 140, ofchamber 120 to expand and contract by extremely small amounts.

The extremely small expansions and contractions of the walls, 130 and140, of chamber 120 of sensor 100 in response to the presence of verylow frequency acoustic signals cause the molecules of fluid in chamber120 (usually molecules of air) to move in low frequency waves throughoutthe cavity 150 of chamber 120. Microphone 110 is capable of detectingthe low frequency waves of molecules of fluid in chamber 120 that arecaused by the low frequency acoustic signal components in the acousticalenergy that cause the walls, 130 and 140, of chamber 120 to expand andcontract.

When microphone 110 receives low frequency acoustic signals thenmicrophone 110 generates electronic signals indicative of the intensityof the low frequency acoustic signals. Electronic processing circuits(shown in FIGS. 6A, 6B and 6C) in a physiological condition monitor 700(shown in FIG. 7) are coupled to microphone 110 through microphoneoutput cables, 170 and 180, to receive and analyze the electronicsignals that are indicative of the intensity of the low frequencyacoustic signals.

The electronic processing circuits comprise electronic filters forfiltering out all components of the signal that are outside thefrequency range of one tenth Hertz (0.1 Hz) to thirty Hertz (30.0 Hz).The electronic processing circuits also comprise electronic filters forfiltering out all components of the signal that are outside thefrequency range of one tenth Hertz (0.1 Hz) to two Hertz (2.0 Hz) toobtain a signal indicative of respiration. The electronic processingcircuits also comprise electronic filters for filtering out allcomponents of the signal that are outside the frequency range of tenHertz (10.0 Hz) to thirty Hertz (30.0 Hz) to obtain a signal indicativeof cardiac activity.

Prior art sensors directly detect higher frequency sounds that are madeby the lungs during respiration or by the heart during cardiac activity.Sensor 100 of the present invention, however, obtains information bydetecting very low frequency signals caused by the motion of the chestduring respiration and by detecting very low frequency signalsassociated with cardiac activity. Almost all of the noise components inan acoustic signal have frequencies that are above the very lowfrequency range. Using the method of the present invention to excludethe higher frequencies of sound (and noise), sensor 100 of the presentinvention eliminates almost all the noise artifacts from the acousticsignal.

An alternate advantageous embodiment of the present invention is shownin FIG. 3. The embodiment shown in FIG. 3 is similar to that shown inFIG. 2 except that chamber 120 of sensor 100 comprises an open endedtube having portions that form an aperture 300. In this embodimentcavity 150 of chamber 120 has access to the surrounding atmospherethrough aperture 300 in the open end of the tube. In the embodimentshown in FIG. 3 microphone 110 is placed within the end wall 140 of theclosed end of the tube.

Alternatively, microphone 110 could be placed within a side wall 130 ofan open ended tube. This embodiment shows that it is possible topractice the invention where the fluid in chamber 120 is air that hasaccess to the air of the surrounding environment.

Although chamber 120 of sensor 100 has been shown in the shape and formof a tube, it is clear that the invention may be practiced with achamber 120 of sensor 100 that has a different type of shape and form.One such alternate embodiment of the present invention is shown in FIG.4.

FIG. 4 shows an exploded view of an alternate advantageous embodiment ofsensor 100 of the present invention. Sensor 100 comprises microphone 110mounted within chamber 120. Microphone 110 may be mounted at anyposition on the interior surface of the bottom 410 of chamber 120. Inthe embodiment of the invention shown in FIG. 4 the shape of chamber 120is rectangular. However, the shape of chamber 120 may be circular,elliptical, or of irregular shape. The height of the walls 420 ofchamber 120 are greater than the height of microphone 110 so that theface 160 of microphone 110 is contained within chamber 120.

Membrane 430 covers the top of chamber 120. Membrane 430 has a shapethat matches the shape of the top of chamber 120. In the embodiment ofsensor 100 shown in FIG. 4, that shape is rectangular. When membrane 430is attached to the top edges of the walls 420 of chamber 120, then acavity 440 is formed between membrane 430 and walls 420 and bottom 410of chamber 120. In one advantageous. embodiment of the presentinvention, the height of the walls 420 are only slightly greater thanthe height of microphone 110 so that the face 160 of microphone 110 ispositioned near membrane 430.

In one advantageous embodiment of the present invention membrane 430 ismade of urethane. However, membrane 430 may also be made of othersuitable materials. Before membrane 430 is attached to the top ofchamber 120 membrane 430 is slightly stretched. The slight stretching ofmembrane 430 is to make membrane 430 taut across the top of chamber 120.

When sensor 100 is used to detect acoustic signals indicative ofphysiological conditions, chamber 120 is placed next to the body (notshown) of the person whose physiological conditions are being monitored.Chamber 120 is placed with the outer surface of membrane 430 adjacent toa selected area of the body. It is not necessary that membrane 430 touchthe skin of the body. There may be a layer of clothing between the skinof the body and membrane 430. Membrane 430 is thereby acousticallycoupled to the area of the body where membrane 430 is placed.

Membrane 430 acquires very low frequency acoustic signals in the form ofvibrations from the area of the body to which it is acousticallycoupled. That is, as the very low frequency acoustic vibrations from thebody impinge upon membrane 430 they cause membrane 430 to vibrate. Thesevibrations of membrane 430 cause the very low frequency acousticvibrations to pass into cavity 440 of chamber 120. The very lowfrequency acoustic vibrations resonate within the enclosed space ofcavity 440.

FIG. 5 shows a cross sectional view of sensor 100 showing cavity 440 andone possible location for the placement of microphone 110 within cavity440. Microphone 110 detects the very low frequency acoustic vibrationsthat are resonating within cavity 440.

The interaction of membrane 430 and resonant cavity 440 increases theamplitude of the very low frequency acoustic signals from the body sothat microphone 110 may more easily detect the signals. The interactionof membrane 430 and resonant cavity 440 accomplishes this increase inacoustic signal strength by forming an acoustic echo chamber in whichmembrane 430 acts as a drumhead and resonant cavity 440 acts as a drum.The resonance of the very low frequency acoustic signals within resonantcavity 440 causes the amplitudes of the acoustic waves within resonantcavity 440 to combine in phase and thereby increase the acoustic signalstrength of the acoustic signals that were originally incident onmembrane 430.

The increase in amplitude of the signals provided by the interaction ofmembrane 430 and resonant cavity 440 enables microphone 110 toefficiently detect signals in the very low frequency range of one tenthHertz (0.1 Hz) to thirty Hertz (30.0 Hz). This very low frequency rangeincludes the very low frequency range used to detect respiration signals(i.e., one tenth Hertz (0.1 Hz) to two Hertz (2.0 Hz)) and the very lowfrequency range used to detect cardiac information signals (i.e., tenHertz (10.0 Hz) to thirty Hertz (30.0 Hz)). The interaction of membrane430 and resonant cavity 440 assists microphone 110 in detecting very lowacoustic signals in the required signal ranges.

To improve reception of the very low frequency acoustic signals, thesurface area of membrane 430 is larger than the surface area of the face160 of microphone 110. In an advantageous embodiment of the presentinvention the surface area of membrane 430 is at least five (5) timesgreater than the surface area of the face 160 of microphone 110. Thepresence of membrane 430 significantly increases the area which may beacoustically coupled to microphone 110. The relatively large area ofmembrane 430 permits larger areas of a body to be analyzed than wouldotherwise be possible.

When microphone 110 receives low frequency acoustic signals thenmicrophone 110 generates electronic signals indicative of the intensityof the low frequency acoustic signals. As described more fully below,electronic processing circuits in physiological condition monitor 700are coupled to microphone 110 through microphone output cables, 170 and180, to receive and analyze the electronic signals that are indicativeof the intensity of the low frequency acoustic signals.

FIGS. 6A, 6B and 6C illustrate circuit diagrams of an advantageousembodiment of circuitry for processing electrical signals from themicrophone of the present invention. As shown in FIG. 6A, microphoneoutput cable 180 is grounded and microphone output cable 170 is coupledto the positive input of operational amplifier 610. The output ofoperational amplifier 610 is fed back to the negative input ofoperational amplifier 610 in order to configure operational amplifier610 as a voltage follower (also known as a buffer amplifier circuit).The voltage follower configuration of operational amplifier 610 acts asa current amplifier for the signal current from microphone 110. Thesignal current that is output from operational amplifier 610 is anamplified version of the signal current from microphone 110. Operationalamplifier 610 may be of the type manufactured by Texas InstrumentsCorporation with product model number TLV2211.

One end of a resistor R1 having a very large value is coupled to thesignal line between microphone 110 and operational amplifier 610. Theother end of resistor R1 is coupled to a reference voltage V_(REF). Atypical value of R1 is one teraohm (1.0 T). One teraohm is equal to onemillion million ohms. A very large resistance is needed to facilitatethe signal processing of the very low frequency signals detected bymicrophone 110. A typical value for reference voltage V_(REF) is onehalf of the voltage of the power supply battery.

The output signal from operational amplifier 610 is coupled viacapacitor C1 to the positive input of operational amplifier 620.Operational amplifier 620 forms part of low bandpass filter circuit 630.Operational amplifier 620 may be of the type manufactured by TexasInstruments Corporation with product model number TLV2211.

A typical value of capacitor C1 is forty seven hundredths of amicrofarad (0.47 μF). One end of resistor R2 is coupled to the signalline between capacitor C1 and operational amplifier 620. The other endof resistor R2 is coupled to the reference voltage V_(REF). A typicalvalue of R2 is five and one tenth megohms (5.1 M)

Low bandpass filter circuit 630 comprises a double pole switch S1 foradjusting the value of the resistance that is coupled in parallel withcapacitor C2. When both poles of switch Si are in the open position,both resistor R5 and resistor R6 are excluded from the circuit. ResistorR5 or resistor R6 (or both) can be selectively included in the circuitby closing the appropriate pole (or both poles) of switch S1.

A typical value for capacitor C2 is thirty three thousands of

a microfarad (0.033 μF). A typical value for resistor R3 is five hundredten kilohms (510.0 K) and a typical value for resistor R4 is two megohms(2.0 M). A typical value for resistor R5 is one megohm (1.0 K) and atypical value for resistor R6 is two megohms (2.0 M).

The output of operational amplifier 620 of low bandpass filter circuit630 appears at the output terminal 640.

FIG. 6B illustrates reference voltage generator circuit 660. The outputof reference voltage generator circuit 660 is the reference voltageV_(REF). The battery voltage V_(cc) is coupled via resistor R7 to thepositive input of operational amplifier 650. Operational amplifier 650forms part of the reference voltage generator circuit 660. Operationalamplifier 650 may be of the type manufactured by Texas InstrumentsCorporation with product model number TLV2211. A typical value ofresistor R7 is five and one tenth megohms (5.1 M).

One end of resistor R8 is coupled to the signal line between resistor R7and operational amplifier 650. The other end of resistor R8 is grounded.Capacitor C3 is coupled in parallel with resistor R8. A typical value ofresistor R8 is five and one tenth megohms (5.1 M). A typical value forcapacitor C3 is one hundredth of a microfarad (0.01 μF).

The output of operational amplifier 650 of reference voltage generatorcircuit 660 appears at the output terminal 670 as V_(REF). The referencevoltage V_(REF) is coupled to the ends of resistor R1, resistor R2 andresistor R3,as indicated in FIG. 6A.

FIG. 6C shows high bandpass filter circuit 680. High bandpass filtercircuit 680 comprises operational amplifier 690. Operational amplifier690 may be of the type manufactured by Texas Instruments Corporationwith product model number TLV2211.

One end of resistor R9 is coupled to the signal line between capacitorC1 and operational amplifier 620. The other end of resistor R9 iscoupled to capacitor C4. A typical value of resistor R9 is thirty threekilohms (33 K). A typical value of capacitor C4 is forty sevenhundredths of a microfarad (0.47 μF). The output of capacitor C4 iscoupled to the negative input of operational amplifier 690. The outputof operational amplifier 690 is fed back via resistor R10 to thenegative input of operational amplifier 690. The positive input ofoperational amplifier 690 is grounded. the A typical value of resistorR10 is thirty three kilohms (33 K)

The output of operational amplifier 690 of high bandpass filter circuit680 appears at the output terminal 695. The function of high bandpassfilter circuit 680 may also be accomplished by utilizing digital signalprocessing methods. For example, the Fast Fourier Transform method maybe utilized to perform the function of high bandpass filter 680.

FIG. 7 is a block diagram of an advantageous embodiment of aphysiological condition monitor 700 that utilizes the low frequencymicrophone sensor 100 of the present invention. As previously described,low frequency microphone sensor 100 receives low frequency signals fromthe body (not shown) of a child whose physiological conditions are beingmonitored. Low frequency microphone sensor 100 detects and amplifiesthose signals as previously described.

As shown in FIG. 7, the output of low frequency microphone sensor 100 iscoupled to an input of low bandpass filter 710. Low bandpass filter 710screens out all frequencies except those frequencies in the frequencybandwidth range from one tenth Hertz (0.1 Hz) to two Hertz (2.0 Hz). Lowbandpass filter 710 may comprise conventional electronic filtercircuits. Low bandpass filter 710 may also comprise electronic circuitrythat utilizes computer software to achieve the bandpass filter functionby digital signal processing. The output of low bandpass filter 710 is adigitally encoded very low frequency signal representative of therespiration of the child being monitored.

The output of low frequency microphone sensor 100 is also coupled to aninput of high bandpass filter 720. High bandpass filter 720 screens outall frequencies except those frequencies in the frequency bandwidthrange from ten Hertz (10.0 Hz) to thirty Hertz (30.0 Hz). High bandpassfilter 720 may comprise conventional electronic filter circuits. Highbandpass filter 720 may also comprise electronic circuitry that utilizescomputer software to achieve the bandpass filter function by digitalsignal processing. The output of high bandpass filter 720 is a digitallyencoded very low frequency signal representative of the cardiac activityof the child being monitored.

The output of low bandpass filter 710 and the output of high bandpassfilter 720 are coupled to processor unit 730. Processor unit 730 iscapable of receiving digitally encoded signals from low bandpass filter710 and from high bandpass filter 720. Battery 735 is coupled toprocessor unit 730 and is capable of supplying electrical power for theoperation of processor unit 730. Although battery 735 is shown coupledonly to processor unit 730 in FIG. 7, battery 735 is connected to andprovides power to all components of physiological condition monitor 700through other electrical connections (not shown). Processor unit 730 iscapable of detecting a signal from battery 735 that indicates that thevoltage level of battery 435 is low.

In one embodiment of the present invention, processor unit 730 iscoupled to radio frequency transmitter 740, which is itself coupled toantenna 750. Processor unit 730 is capable of selectively causing radiofrequency transmitter 740 to transmit digitally encoded signals from lowband pass filter 710 and digitally encoded signals from high band passfilter 720 to base station unit 760 via transmitter 740 and antenna 750.The digitally encoded signals are received by base station unit 760 viaantenna 765. The received signals may then be displayed and analyzed atbase station unit 760.

Processor unit 730 is capable of causing radio frequency transmitter 440to transmit a signal to base station unit 760 that indicates that thevoltage level of battery 735 is low. Processor unit 730 is also capableof causing radio frequency transmitter 740 to transmit a signal to basestation unit 760 that indicates that processor unit 730 is not receivingsignals from low bandpass filter 710 or from high bandpass filter 720.That is, processor unit 730 can transmit to base station unit 760 asignal indicating that one (or both) of the physiological conditions(breathing and heartbeat) is not being monitored.

Base station unit 760 is capable of sounding an alarm if an analysis ofthe received signals indicates an abnormal condition in the child beingmonitored. Base station unit 760 comprises speaker 767 which may beactivated to sound an alarm when base station unit 760 receives one ormore signals indicating that (1) the child's breathing is irregular orhas stopped, or (2) the child's heartbeat is irregular or has stopped,or (3) the child's breathing is not being monitored, or (4) the child'sheartbeat is not being monitored, or (5) the battery voltage level istoo low. Base station unit 760 is to be placed where the one of thechild's parents can hear the alarm whenever the alarm sounds.

In this manner, the child's care giver can immediately respond to thealarm to determine what condition exists. If the child is inphysiological distress, the child's care giver can immediately attemptto relieve that distress. For example, if the child has ceasedbreathing, the care giver could immediately administer cardiopulmonaryresuscitation (CPR) to the child. If the alarm indicates a low batteryor failure of monitoring function, remedial steps can be takenimmediately.

In one advantageous embodiment of physiological condition monitor 700, amonitor housing 800 contains low frequency microphone sensor 100, lowbandpass filter 710, high bandpass filter 720, processor unit 730,battery 735, transmitter 740 and antenna 750. An advantageous embodimentof monitor housing 800 will be described in connection with FIGS. 8 to21. Monitor housing 800 is capable of being coupled to a belt, harnessor item of clothing that may be worn by the child being monitored. Inthis embodiment of physiological condition monitor 700 the movements ofthe child being monitored are not restricted.

In an alternate advantageous embodiment of physiological conditionmonitor 700 processor unit 730 is coupled to recording device 770.Processor unit 730 sends digitally encoded signals from low band passfilter 710 and digitally encoded signals from high band pass filter 720to recording device 770. Recording device 770 is preferably anon-volatile data storage device such as a magnetic tape recorder or aflash memory data storage card. A non-volatile data storage device is adevice that retains the data stored in it when external power to thedevice is shut off.

In an additional advantageous embodiment of physiological conditionmonitor 700 processor unit 730 is coupled to network interface unit 780.Network interface unit 780 is capable of being coupled to a computernetwork such as a local area network (LAN), or a wide area network(WAN), or the Internet. The connection of network interface unit 780 toa computer network may be a wired connection or wireless connection.

In FIG. 7 network interface unit 780 is shown coupled to the Internet790 via an Internet protocol router 785. Processor unit 730 sendsdigitally encoded signals from low band pass filter 710 and digitallyencoded signals from high band pass filter 720 to network interface unit780. Network interface unit 780 adapts the data to be transmitted viaInternet protocol router 785 to the Internet 790. In this manner thedata can be sent to medical monitoring station 795 at a remote location.Medical monitoring station 795 can be located in a hospital, a doctor'soffice, a clinic, a care giver facility, or any similar type oflocation.

In an alternate advantageous embodiment of physiological conditionmonitor 700 processor unit 730 is not coupled to transmitter 740 and toantenna 750. Instead processor unit 730 is coupled directly by wire to awired base station unit (not shown) of the type described above. Thewired base station unit is usually located in a console by the child'sbed. As in the previously described case of base station unit 760, thewired base station unit is capable of displaying and analyzing digitallyencoded signals from processor unit 730. The wired base station unit iscapable of sounding an alarm if an analysis of the digitally encodedsignals indicates an abnormal condition in the child. In this embodimentthe wires coupling the physiological condition monitor 700 to the wiredbase unit do restrict the movements of the child.

FIGS. 8 though 21 depict an advantageous embodiment of monitor housing800 of physiological condition monitor 700 that is shown in FIG. 7. FIG.8 shows a perspective top view of monitor housing 800. FIG. 9 shows aperspective bottom view of monitor housing 800. The top half of monitorhousing 800 comprises a top housing 810 and the bottom half of monitorhousing 800 comprises a bottom housing 820. As shown in FIG. 8 and FIG.9, top housing 810 and bottom housing 820 fit together to enclose theelements of physiological condition monitor 700. Top housing 810 andbottom housing 820 are formed having portions that define a cavitywithin monitor housing 800 to receive battery 735 that is shown in FIG.7. In this embodiment battery 735 is a flat, cylindrically symmetrical,coin-shaped battery of the type commonly used in cameras and otherportable electronic equipment.

Bottom housing 820 is formed having portions that receive a battery door830 that may be opened and closed to allow access to place and removebattery 735 within. the interior of monitor housing 800. Battery door830 is pivotally connected to bottom housing 820 and may be opened andclosed by pivotally moving battery door 830 with respect to bottomhousing 820. Battery door 830 is shown in closed position in FIG. 9.

The outer surface of membrane 430 of low frequency microphone sensor 100is also shown in FIG. 9. In this advantageous embodiment of the presentinvention, membrane 430 (and cavity 440) has an geometrically irregularshape. The shape generally comprises two curves of different radiispaced apart and bounded on the ends by relatively flat surfaces.

FIG. 10 shows an exploded view of monitor housing 800. Top housing 810has portions that receive a pivotal hinge boss 1010 and allow hinge boss1010 to rotate. Hinge boss 1010 pivotally couples battery door 830 totop housing 810 and bottom housing 820. Battery door 830 is formedhaving portions that define a passageway 1020 through battery door 830for receiving the lower end of hinge boss 1010. After the lower end ofhinge boss 1010 has been placed through passageway 1020 of battery door830, retaining ring 1030 fastens battery door 830 to hinge boss 1010.

In FIG. 10 battery 735 is shown in position within monitor housing 800.Battery support plate 1040 covers the top of battery 735 and only thelower edge of battery 735 is visible in FIG. 10. Two battery retainingpins 1050 are placed along the interior of bottom housing 820 to keepbattery 735 in its place within monitor housing 800 and to contact thepositive and negative terminals of battery 735.

Microphone 110 of low frequency microphone sensor 100 is shown in FIG.10. To support microphone 110 within the structure of monitor housing800 microphone 110 is placed through microphone sleeve 1060. In thisadvantageous embodiment of the invention microphone 110 extends throughan aperture 1070 in the bottom of chamber 120 and extends into cavity440. The interior of chamber 120 and cavity 440 are not visible in FIG.10.

Printed circuit board 1080 supports the electronic circuitry ofphysiological condition monitor 700 that has been previously described.Lens 1090 is provided to permit a signal light such as a light emittingdiode (not shown) to send signals concerning the operational status ofphysiological condition monitor 700.

FIG. 11 is a plan view of the top housing 810 of monitor housing 800.The location of hinge boss 1010 is shown at one corner of top housing810. Also shown are the locations of four passageways 1110 for receivingfasteners such as screws (not shown) for fastening top housing 810 tobottom housing 820. The location of lens 1090 is also shown. Therectangles that are shown in dotted outline in the center of the planview of top housing 810 represent the locations of electronic circuitry(such as processor unit 730) that are mounted on underlying printedcircuit board 1080. The two circles that are visible in the center ofthe plan view of top housing 810 represent the locations of tworeceptacles 1120 for receiving fasteners such as screws (not shown) forprinted circuit board 1080 to top housing 810.

FIG. 12 is a plan view of bottom of the assembled monitor housing 800.The location of hinge boss 1010 and retaining ring 1030 is shown at onecorner of bottom housing 820. Battery door 830 is shown in its closedposition. Also shown are the locations of four passageways 1110 forreceiving fasteners such as screws (not shown) for fastening top housing810 to bottom housing 820. The rectangles that are shown in dottedoutline in the center of bottom housing 820 represent the locations ofelectronic circuitry (such as processor unit 730) that are mounted onunderlying printed circuit board 1080. The location of microphone 110within cavity 440 is also shown. Membrane 430 (not shown in FIG. 12)covers the top of cavity 440.

FIG. 13 is a cross sectional view of top housing 810 of monitor housing800 taken along line 13—13 of FIG. 11. A side view of receptacle 1120 isshown. Because the line 13—13 takes a right angle turn, only onereceptacle 1110 is shown. FIG. 14 is a cross sectional view of tophousing 810 of monitor housing 800 taken along line 14—14 of FIG. 11.Both receptacles 1320 are shown. Also shown is the location of hingeboss 1010.

FIG. 15 is a plan view of bottom housing 820 of monitor housing 800. Thelocation of microphone 110 is shown. Also shown in the location andshape of membrane 430 and the underlying cavity 440 (not shown in FIG.15). The location of fastener receptacles 1110 are also shown. Thecircular area 1510 shows the location of battery 735 (not shown in FIG.15) within monitor housing 800. Oblong area 1520 shows the location ofbattery door 830 (also not shown in FIG. 15).

FIG. 16 is a side elevation view of bottom housing 820 of monitorhousing 800 taken along line 16—16 of FIG. 15. A portion of the bottomof bottom housing 820 is covered with membrane 430. The location ofcavity 440 in bottom housing 820 is shown. Also shown is the location ofmicrophone 110 and fastener receptacles 1110. FIG. 17 is an endelevation view of bottom housing 820 of monitor housing 800 taken alongline 17—17 of FIG. 15. FIG. 17 also shows the location of membrane 430,cavity 440 and microphone 110.

FIG. 18 is a plan view of battery door 830 of monitor housing 800. Theshape of battery door 830 fits the oblong area 1520 shown in FIG. 15. Aspreviously mentioned, battery door 830 is formed having portions thatdefine a passageway 1020 through battery door 830 for receiving thelower end of hinge boss 1010. Passageway 1020 is shown in FIG. 18. Alsoshown is latch 1810 for latching battery door 830 after it has beenclosed. FIG. 19 is a side elevation view of battery door 830 of monitorhousing 800 taken along line 19—19 of FIG. 18. FIG. 20 is an endelevation view of battery door 830 of monitor housing 800 taken alongline 20—20 of FIG. 18.

FIG. 21 is a perspective bottom view of monitor housing 800 ofphysiological condition monitor 700 showing battery door 830 in an openposition and showing the placement of battery 735 in monitor housing800. The location of microphone 110 within cavity 440 is shown. The endof hinge boss 1010 and retaining ring 1030 are also shown.

Although the present invention has been described with reference tomonitoring the physiological conditions of human beings, the presentinvention can also be used to monitor the physiological conditions ofvertebrate animals such as dogs, cats, horses, and the like.

Although the present invention has been described in detail, thoseskilled in the art should understand that they can make various changes,substitutions and alterations herein without departing from the spiritand scope of the invention in its broadest form.

What is claimed is:
 1. An apparatus for remotely monitoring at least onephysiological condition of a child by detecting very low frequencyacoustic signals comprising a low frequency sensor capable of beingacoustically coupled to a source of acoustic signals, said low frequencysensor capable of receiving low frequency acoustic signals in thefrequency range of one tenth Hertz to thirty Hertz and generatingelectronic signals indicative of the intensity of said low frequencyacoustic signals.
 2. An apparatus as claimed in claim 1 furthercomprising signal processing circuitry coupled to said low frequencysensor capable of processing said electronic signals from said lowfrequency sensor to obtain electronic signals indicative of theintensity of said low frequency acoustic signals in the frequency rangeof one tenth Hertz to two Hertz.
 3. An apparatus as claimed in claim 1further comprising signal processing circuitry coupled to said lowfrequency sensor capable of processing said electronic signals from saidlow frequency sensor to obtain electronic signals indicative of theintensity of said low frequency acoustic signals in the frequency rangeof ten Hertz to thirty Hertz.
 4. The apparatus as claimed in claim 1wherein said low frequency sensor comprises: a chamber capable of beingacoustically coupled to a source of acoustic signals, said chamberhaving portions that define a cavity within said chamber; a microphonecapable of receiving low frequency acoustic signals within said cavityof said chamber in the frequency range of one tenth Hertz to thirtyHertz and capable of generating electronic signals indicative of theintensity of said low frequency acoustic signals.
 5. The apparatus asclaimed in claim 4 wherein said chamber is a closed chamber filled withfluid.
 6. The apparatus as claimed in claim 5 wherein said fluid is air.7. The apparatus as claimed in claim 4 wherein said chamber is an openchamber filled with air.
 8. The apparatus as claimed in claim 4 whereinsaid chamber is formed having nonrigid walls.
 9. The apparatus asclaimed in claim 8 wherein said nonrigid walls are capable of movinginwardly and outwardly with respect to the interior of said cavity inresponse to the presence of low frequency acoustic energy.
 10. Anapparatus as claimed in claim 4 further comprising signal processingcircuitry coupled to said microphone capable of processing saidelectronic signals from said microphone to obtain electronic signalsindicative of the intensity of said low frequency acoustic signals inthe frequency range of one tenth Hertz to two Hertz.
 11. An apparatus asclaimed in claim 4 further comprising signal processing circuitrycoupled to said microphone capable of processing said electronic signalsfrom said microphone sensor to obtain electronic signals indicative ofthe intensity of said low frequency acoustic signals in the frequencyrange of ten Hertz to thirty Hertz.
 12. An apparatus for remotelymonitoring at least one physiological condition of a child by detectingvery low frequency acoustic signals comprising an apparatus capable ofdetecting very low frequency acoustic signals in the frequency range ofone tenth Hertz to thirty Hertz comprising: a chamber capable of beingacoustically coupled to a source of acoustic signals, said chamberhaving portions that define a cavity within said chamber, and saidchamber having nonrigid walls capable of moving inwardly and outwardlywith respect to the interior of said cavity in response to the presenceof low frequency acoustic energy; and a microphone placed within saidcavity of said chamber capable of receiving low frequency acousticsignals within said cavity of said chamber that are caused by the inwardand outward motion of said nonrigid walls of said cavity, and capable ofgenerating electronic signals indicative of the intensity of said lowfrequency acoustic signals.
 13. The apparatus as claimed in claim 4further comprising: a membrane attached to said chamber covering saidcavity of said chamber, said membrane capable of moving in response tovery low frequency acoustic signals incident on said membrane to causesaid very low frequency acoustic signals to be transmitted through saidcavity to said microphone.
 14. The apparatus as claimed in claim 13wherein the movements of said membrane amplify the intensity of saidvery low frequency acoustic signals within said cavity.
 15. Theapparatus as claimed in claim 14 wherein said movements of said membraneamplify the intensity of said very low frequency acoustic signals withinsaid cavity by causing said very low frequency acoustic signals toresonate within said cavity.
 16. An apparatus as claimed in claim 13further comprising signal processing circuitry coupled to saidmicrophone capable of processing said electronic signals from saidmicrophone to obtain electronic signals indicative of the intensity ofsaid low frequency acoustic signals in the frequency range of one tenthHertz to two Hertz.
 17. An apparatus as claimed in claim 13 furthercomprising signal processing circuitry coupled to said microphonecapable of processing said electronic signals from said microphonesensor to obtain electronic signals indicative of the intensity of saidlow frequency acoustic signals in the frequency range of ten Hertz tothirty Hertz.
 18. The apparatus as claimed in claim 12 furthercomprising: a membrane attached to said chamber covering said cavity ofsaid chamber, said membrane capable of moving in response to very lowfrequency acoustic signals incident on said membrane to cause said verylow frequency acoustic signals to be transmitted through said cavity tosaid microphone.
 19. The apparatus as claimed in claim 18 wherein themovements of said membrane amplify the intensity of said very lowfrequency acoustic signals within said cavity.
 20. The apparatus asclaimed in claim 19 wherein said movements of said membrane amplify theintensity of said very low frequency acoustic signals within said cavityby causing said very low frequency acoustic signals to resonate withinsaid cavity.
 21. A physiological condition monitor for remotelymonitoring at least one physiological condition of a child by detectingvery low frequency acoustic signals of the child comprising: a sensorcapable of being acoustically coupled to the body of the child beingmonitored and capable of receiving low frequency acoustic signals in therange of one tenth Hertz to thirty Hertz and capable of generatingelectronic signals indicative of the intensity of said low frequencyacoustic signals; and a low bandpass filter coupled to said sensorcapable of processing said electronic signals from said sensor to obtaindigitally encoded electronic signals indicative of the intensity of saidlow frequency acoustic signals in the frequency range of one tenth Hertzto two Hertz, said digitally encoded electronic signals being indicativeof respiration activity of the child being monitored.
 22. Thephysiological condition monitor claimed in claim 21 further comprising:a high bandpass filter coupled to said sensor capable of processing saidelectronic signals from said sensor to obtain digitally encodedelectronic signals indicative of the intensity of said low frequencyacoustic signals in the frequency range of ten Hertz to thirty Hertz,said digitally encoded electronic signals being indicative of cardiacactivity of the child being monitored.
 23. The physiological conditionmonitor claimed in claim 22 further comprising: a processor unit, saidprocessor unit coupled to said low bandpass filter capable of receivingsaid digitally encoded electronic signals from said low bandpass filterindicative of said respiration activity, and said processor unit coupledto said high bandpass filter capable of receiving said digitally encodedelectronic signals from said high bandpass filter indicative of saidcardiac activity; and a recording device associated with said processorunit capable of receiving from said processor unit digitally encodedelectronic signals representative of at least one physiologicalcondition and capable of recording said electronic signals.
 24. Thephysiological condition monitor as claimed in claim 23 furthercomprising a transmitter coupled to. said processor unit capable ofreceiving digitally encoded electronic signals indicative of at leastone physiological condition, said transmitter including an antenna fortransmitting said digitally encoded electronic signals received fromsaid processor unit.
 25. A sensor capable of obtaining low frequencyacoustic signals from a child without being directly coupled to the skinof the child, said sensor comprising: a chamber having portions thatdefine a cavity within said chamber, said chamber capable of beingacoustically coupled to low frequency acoustic signals of the child; amicrophone placed within said cavity of said chamber, said microphonecapable of receiving low frequency acoustic signals in the frequencyrange of one tenth Hertz to thirty Hertz and generating electronicsignals indicative of the intensity of said low frequency acousticsignals received by said microphone; and a membrane attached to saidchamber covering said cavity of said chamber, said membrane capable ofmoving in response to very low frequency acoustic signals incident uponsaid membrane to cause said very low frequency acoustic signals to betransmitted through said cavity to said microphone, said membranecapable of being acoustically coupled to said low frequency acousticsignals of the child without directly contacting the skin of the child.26. A method for detecting low frequency acoustic signals comprising thesteps of: forming a chamber having portions that define a cavity withinsaid chamber; placing a microphone within said cavity of said chamber;attaching a membrane to said chamber covering said cavity of saidchamber; acoustically coupling said membrane to a source of acousticsignals; receiving in said microphone low frequency acoustic signals inthe range of one tenth Hertz to thirty Hertz; and generating in saidmicrophone electronic signals indicative of the intensity of said lowfrequency acoustic signals.
 27. The method as claimed in claim 26further comprising the steps of: coupling a low bandpass filter to saidmicrophone capable of processing said electronic signals from saidmicrophone; obtaining digitally encoded electronic signals indicative ofthe intensity of. said low frequency acoustic signals in the frequencyrange of one tenth Hertz to two Hertz; coupling a high bandpass filterto said microphone capable of processing said electronic signals fromsaid microphone; and obtaining digitally encoded electronic signalsindicative of the intensity of said high frequency acoustic signals inthe frequency range of ten Hertz to thirty Hertz.
 28. The method asclaimed in claim 27 further comprising the steps of: coupling aprocessor unit to said low bandpass filter and to said high bandpassfilter; receiving in said processor unit said digitally encodedelectronic signals from said low bandpass filter; receiving in saidprocessor unit said digitally encoded electronic signals from said highbandpass filter; coupling a recording device to said processor unit; andreceiving in said recording device said digitally encoded electronicsignals from said processor unit; and recording in said recording devicesaid digitally encoded electronic signals.
 29. The method as claimed inclaim 26 further comprising the steps of: acoustically coupling saidmembrane to low frequency acoustic signals of a child; and positioningsaid membrane so that said membrane does not contact the skin of thechild.